|Publication number||US6875212 B2|
|Application number||US 10/327,706|
|Publication date||Apr 5, 2005|
|Filing date||Dec 20, 2002|
|Priority date||Jun 23, 2000|
|Also published as||CA2510731A1, CN1787785A, CN100588374C, EP1589886A2, US8337556, US20040006341, US20050149022, WO2004058045A2, WO2004058045A3|
|Publication number||10327706, 327706, US 6875212 B2, US 6875212B2, US-B2-6875212, US6875212 B2, US6875212B2|
|Inventors||Samuel M. Shaolian, George P. Teitelbaum, Thanh Van Nguyen, To V. Pham, Richard H. Estes|
|Original Assignee||Vertelink Corporation|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (57), Non-Patent Citations (4), Referenced by (213), Classifications (38), Legal Events (7)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This is a continuation-in-part of U.S. patent application Ser. No. 10/161,554, filed on May 31, 2002, which is a continuation-in-part of U.S. patent application Ser. No. 09/976,459, filed on Oct. 10, 2001, now U.S. Pat. No. 6,749,614, which is a continuation-in-part of U.S. patent application Ser. No. 09/943,636, filed on Aug. 29, 2001, which is a continuation-in-part of U.S. patent application Ser. No. 09/747,066, filed on Dec. 21, 2000, which claims priority to U.S. Provisional Patent Application No. 60/213,385, filed Jun. 23, 2000, entitled “Percutaneous Interbody Fusion Device,” the contents of each of which are incorporated in their entirety into this disclosure by reference
1. Field of the Invention
The present invention relates to medical devices and, more particularly, to systems for forming orthopedic fixation or stabilization implants in place within the body, such as by infusing a formable media into a cavity. In one application, the present invention relates to minimally invasive procedures and devices for forming a spinal stabilization rod in situ.
2. Description of the Related Art
The human vertebrae and associated connective elements are subject to a variety of diseases and conditions which cause pain and disability. Among these diseases and conditions are spondylosis, spondylolisthesis, vertebral instability, spinal stenosis and degenerated, herniated, or degenerated and herniated intervertebral discs. Additionally, the vertebrae and associated connective elements are subject to injuries, including fractures and torn ligaments and surgical manipulations, including laminectomies.
The pain and disability related to these diseases, conditions, injuries and manipulations often result from the displacement of all or part of a vertebra from the remainder of the vertebral column. A variety of methods have been developed to restore the displaced vertebrae or portions of displaced vertebrae to their normal position and to fix them within the vertebral column. For example, open reduction with screw fixation is one currently used method. The surgical procedure of attaching two or more parts of a bone with pins, screws, rods and plates requires an incision into the tissue surrounding the bone and the drilling of one or more holes through the bone parts to be joined. Due to the significant variation in bone size, configuration, and load requirements, a wide variety of bone fixation devices have been developed in the prior art. In general, the current standard of care relies upon a variety of metal wires, screws, rods, plates and clamps to stabilize the bone fragments during the healing or fusing process. These methods, however, are associated with a variety of disadvantages, such as morbidity, high costs, lengthy in-patient hospital stays and the pain associated with open procedures.
Therefore, devices and methods are needed for repositioning and fixing displaced vertebrae or portions of displaced vertebrae which cause less pain and potential complications. Preferably, the devices are implantable through a minimally invasive procedure.
In accordance with one embodiment, there is provided a formed in place orthopedic device. The device comprises an outer wall, defining a cavity therein and a hardenable media within the cavity to form the orthopedic device, said hardenable media comprising a resin and hardener mixture that is substantially cured at a temperature below about 45° C. in about 90 minutes or less, wherein the hardenable media is hardened while the device is positioned within the body of a patient to create the formed in place orthopedic device.
In accordance with another embodiment, there is provided a bone fixation device. The device comprises a delivery catheter comprising an inflatable member, a hardenable media contained within the inflatable member, and at least two anchors having portals, wherein the inflatable member extends through the portals of the anchors. The hardenable media comprises an epoxy that cures to a hardened form having a static compression bending value (ASTM F1717) of at least 90 lbs in about 90 minutes or less.
In accordance with another embodiment, there is provided an orthopedic fixation device. The device comprises an elongate, flexible tubular body having a distal end and a proximal end, said body forming a central lumen, a manifold at the proximal end of the tubular body comprising at least one port, an inflatable member having a proximal end, a distal end, and an interior, removably attached to the distal end of the tubular body a hardenable media for inflating said inflatable member, said hardenable media comprising about 45-52% by weight aromatic diepoxide resin, about 19-23% by weight aliphatic diepoxide resin, about 20-29% by weight dialkylamines and about 4-9% cycloalkylamines; and a valve, provided at the proximal end of the inflatable member.
In accordance with another embodiment, there is provided a method of forming an orthopedic device at a treatment site within the body of a patient, comprising the steps of positioning an outer wall at the treatment site within the patient, the outer wall defining a chamber therein, and introducing a hardenable media into the chamber, wherein the hardenable media cures from a liquid form to a hardened form having a static compression bending value of at least 90 lbs (ASTM F1717) in about 90 minutes or less.
In accordance with another embodiment, there is provided a method of stabilizing an orthopedic fracture, comprising inserting at least two anchors having portals into a bone, delivering an orthopedic device comprising an inflatable balloon to the bone, and inflating said balloon with a hardenable media comprising about 45-52% by weight aromatic diepoxide resin, about 19-23% by weight aliphatic diepoxide resin, about 20-29% by weight dialkylamines and about 4-9% cycloalkylamines, wherein said orthopedic device extends through said portals, such that said inflating fixes said anchors in relation to one another.
In accordance with another embodiment, there is provided a method of stabilizing an orthopedic fracture, comprising inserting at least two anchors having portals into a bone, delivering an orthopedic device comprising an inflatable balloon through the portals, and inflating said balloon with a liquid curable material, wherein the inflating step fixes said anchors in relation to one another and the curable material is substantially cured at a temperature below about 45° C. in about 90 minutes or less. In another embodiment, there is provided a formed in place medical device, comprising an outer wall, defining a cavity therein and a hardenable media within the cavity to form the medical device, said hardenable media comprising a resin and hardener mixture that cures at a temperature below about 45° C. wherein said cured media has a static compression bending value (ASTM F1717) of at least 150 lbs wherein the hardenable media is hardened while the device is positioned within the body of a patient to create the formed in place medical device.
In preferred embodiments, the hardenable or curable material comprises about 45-52% by weight aromatic diepoxide resin, about 19-23% by weight aliphatic diepoxide resin, about 20-29% by weight dialkylamines and about 4-9% cycloalkylamines. In an especially preferred embodiment, the aromatic diepoxide resin comprises diglycidyl ether of Bisphenol A or diglycidyl ether of Bisphenol F; the aliphatic diepoxide resin comprises one or more alkane diols of glycidyl ether; the cycloalkylamines are N-aminoalkylpiperazines; and the dialkylamines are according to the formula H2N—R—NH2, wherein R is a branched or unbranched C2-C10 alkyl group. The hardenable media, when substantially cured, preferably has a static compression bending value (ASTM F1717) of at least about 60 lbs, and at least about 100 lbs when fully cured. The media is preferably substantially cured in about 90 minutes or less, and the curing takes place at a temperature of about 45° C. or less, more preferably about 43° C. or less.
Further features and advantages of the present invention will become apparent to those of skill in the art in view of the detailed description of preferred embodiments which follows, when considered together with the attached claims and drawings.
Although the application of the present invention will be disclosed primarily in connection with a spinal fixation procedure, the methods and devices disclosed herein are intended for use in any of a wide variety of medical applications where formation of an attachment, bulking, support, fixation or other element in situ may be desirable.
One advantage of the in situ prosthesis formation in accordance with the present invention is the ability to obtain access to a treatment site through a minimally invasive access pathway, while enabling the formation of a relatively larger implant at the treatment site. This allows procedure morbidity to be minimized, since open surgical cutdowns or other invasive access procedures may be avoided. In addition, the in situ formation in accordance with the present invention allows the formation of an implant having any of a wide variety of customized or predetermined shapes, due to the ability of the infusible hardenable media to assume the shape of the cavity or flexible container into which it is infused.
The methods and devices of the present invention additionally enable access to a treatment site within the body along a curved and even tortuous pathway, through which a preformed prosthesis would not fit or would not be navigable. The detachable inflatable prosthesis of the present invention, removably coupled to the distal end of an elongate flexible tubular catheter body, can be dimensioned for percutaneous, surgical or transluminal advancement and deployment of an inflatable or otherwise curable in place prosthesis in any of a wide variety of orthopedic applications, such as the spine as disclosed in greater detail below, as well as long bones, short bones, and associated ligaments and tendons. In addition, the deployment catheter and prosthesis can be dimensioned for transluminal navigation throughout the cardiovascular system, the gastrointestinal tract, the biliary tract, the genitourinary tract, or the respiratory tract (e.g. the tracheobronchial tree). The device may thus be advanced through artificial access pathways as well as naturally occurring lumens and hollow organs. Additional applications of the in situ device formation technology of the present invention will become apparent to those of skill in the art in view of the disclosure herein.
In connection with spinal fixation applications, the present invention involves inserting one or two or more bone anchors having a connector such as a portal into at least a first and a second adjacent or nonadjacent vertebra. An implantable, inflatable orthopedic device is inserted through the portals and inflated to lock to the bone anchors and stabilize the bone components. A deployment system, comprising a delivery catheter removably carrying the implantable device, is provided, such that the procedure may be conducted in a percutaneous or minimally invasive manner to minimize procedure trauma to the patient.
The deployment system shown in
The overall length and cross sectional dimensions of the delivery catheter 100 may be varied, depending upon the intended clinical application. In a device intended for percutaneous or minimally invasive fusion of lumbar and/or sacral vertebrae, for example, the tubular body 104 will generally have a length within the range of from about 15 cm to about 50 cm, and a diameter within the range of from about 2 mm to about 6 mm.
Percutaneous insertion of the delivery catheter 100 may be facilitated by the provision of a removable elongate stiffening wire 122, extending through a lumen such as inflation lumen 130 (see
The deployment device 100 further comprises a manifold 124, located at the proximal end 106 of the elongate tubular body 104. The catheter manifold 124 provides a maneuvering handle for the health care professional, and supports an inflation port 126 and a vent port 128. Either or both the inflation port 126 or the vent port 128 may be provided with a coupling, such as a luer-lock fitting for connection to associated devices as is known in the art. For example, a luer or other connector on the inflation port 126 facilitates connection to a source of pressurized inflation media in a conventional manner. The vent port 128 may be connected to a syringe or other device to draw a vacuum, to evacuate air from the balloon prior to infusion of the hardenable media.
The manifold 124 may also include an injection port for allowing injection of radiopaque contrast fluid to enable visualization of the delivery device on a fluoroscope. The proximal manifold 124 may be machined or injection molded of any of a variety of known suitable materials such as PTFE, ABS, nylon, polyethylene, polycarbonate, or others known in the art. A precision gasket may also be provided, which seals securely around the inner sleeve 110, prohibiting fluid loss.
Catheter manufacturing techniques are generally known in the art, including extrusion and coextrusion, coating, adhesives, and molding. The catheter of the present invention is preferably made in a conventional manner. The elongate shaft of the catheter may be extruded, using polymers such as Nylon, PEBAX, PEEK, PTFE, PE or others known in the catheter arts, the stiffness of which may be selected as appropriate. Material selection varies based on the desired characteristics. The joints are preferably bonded. Biocompatible adhesives or heat bonding may be used to bond the joints. The balloon and stent are also made in a conventional manner or in any suitable manner.
The deployment system 100 further comprises an implantable inflatable orthopedic device 102, which may function, in a spinal fusion application, as an inflatable or formed in place fixation plate or rod. Implantable device 102 is removably carried by the distal end of the tubular body 104, such that inflation lumen 130 is in communication with the interior cavity 146 of the inflatable device 102. The inflation media may thus be infused through inflation port 126 (or opening 127) located at manifold 124 to fill the cavity 146.
The implantable device 102, which may be a balloon 114, includes a proximal end 116, a distal end 118, and a flexible wall 148. The balloon 114 may be formed from any of a variety of polymeric materials which are known in the balloon angioplasty arts. These include, for example, complaint materials such as polyethylene, polyethylene blends or nylon, and substantially noncompliant materials such as polyethylene terephthalate. Any of a wide variety of other biocompatible polymers may be utilized, as will be apparent to those of skill in the art in view of the disclosure herein.
The balloon 114 may comprise a single or multiple layers, depending upon the desired physical properties. In one embodiment, the balloon comprises two layers, having a reinforcing structure such as a stent or a plurality of axially extending support strips sandwiched therebetween. In an alternate embodiment, the balloon 114 comprises a first, inner layer which restrains the hardenable media. A second, outer layer is coaxially disposed about the first layer, and is provided with a plurality of apertures or a microporous structure. An infusion lumen is provided in the elongate tubular body, for providing communication between a proximal infusion port and the space in between the inner and outer balloon layers. In this manner, fluids, which may contain any of a variety of medications, can be infused into the tissue surrounding the treatment site. Suitable structures and manufacturing considerations are disclosed in U.S. Pat. No. 5,295,962 to Crocker et al., the disclosure of which is incorporated in its entirety herein by reference.
Although a cylindrical configuration for balloon 114 is illustrated herein, any of a variety of alternative cross sectional configurations may be utilized. The overall length, diameter and wall thickness of the implantable inflatable orthopedic device 102 may be varied, depending on the particular treatment and access site. In one embodiment, device 102 has an inflated length between about 2 and 12 cm, and often between about 5 cm and about 8 cm for adjacent vertebrae fixation. The device 102 has an inflated diameter of generally between about 0.5 and 2 cm.
The length of the balloon 114 is based upon the anticipated distance between the first and second anchors, or, in an embodiment having more than two anchors, between the anchors having the greatest axial separation. For example, in a fusion application in which two adjacent lumbar vertebrae (e.g. L4-L5) are to be fused in an adult, the first and second anchors will generally be spaced apart by a distance within the range of from about 5 cm to about 8 cm. Preferably, the axial length of the balloon 114 is sufficiently longer than the inter anchor spacing to permit a portion of the balloon to expand on the “far” side of the anchor aperture as is illustrated, for example, in FIG. 9. Thus, balloon lengths for the above identified inter anchor distances will generally exceed the sum of the inter anchor distance and the anchor diameters by at least about 0.5 cm. Preferably, the balloon extends at least about 1 cm beyond the portals.
For use in an application where a first vertebrae is attached to a second vertebrae, and the second vertebrae is separated from the first vertebrae by at least a third vertebrae, for example in the lumbar spine, the inter anchor distance will generally be within the range of from about 10 cm to about 20 cm. As will be appreciated by those of skill in the art, in a three or more vertebrae fixation, the intermediate vertebra or vertebrae will normally but need not necessarily be connected to the inflatable balloon 114. Thus, in one application, the balloon 114 connects a first attachment point at a first bone and a second attachment point at a second bone, with one or more intermediate bones unconnected to the balloon 114. In another application, at least a third anchor is provided in between the first and second anchors, and the balloon 114 is threaded through an aperture on each of the first, second and third anchors. The desirability of attaching or leaving unattached intervening vertebrae or other bones or structures between two attachment points is a matter of clinical judgement, in view of the particular circumstances of the patient.
The primary function of the balloon 114 is to influence or control the shape of the hardenable media, following injection therein. The implantable balloon 114 is not normally required to restrain pressure over an extended period of time. Thus, a greater design flexibility may be permitted, compared to conventional angioplasty or other dilatation balloons. For example, the balloon 114 may be porous, either for drug delivery as has been discussed, or to permit osteoincorporation and/or soft tissue ingrowth.
Certain hardenable media which may be utilized in connection with the present invention, such as PMMA, have a significantly greater viscosity in the precured form, compared to conventional angioplasty balloon inflation media. In addition, since the balloon 114 is not intended to contain significant pressure, conventional high strength materials such as for high pressure angioplasty may not be necessary. This allows the balloon 114 to be constructed in any of a variety of ways, including techniques utilized for balloon angioplasty applications. In addition, the balloon 114 (or balloon-like structure) may be made out of any of a wide variety of woven or nonwoven fibers, fabrics, metal mesh such as woven or braided wires, and carbon. Biocompatible fabrics or sheet material such as ePTFE and Dacron® may also be used.
The hardenable media is preferably a rapid setting, low viscosity, liquid polymer or polymer precursor, such as polymethyl methacrylate. However, any of a variety of other materials which provide the required stiffening or setting characteristics may be used, including any of a variety of epoxies, polyurethane or blends of polyurethane-silicone.
In the context of a rod shaped inflatable container, for use in spinal fixation procedures, the physical requirements of the hardenable media will depend upon the length and diameter of the rod as well as the physical requirements imposed by the implantation site. For certain embodiments, polymethyl methacrylate, epoxy, polyurethane or other particular material may or may not exhibit sufficient physical properties. Physical properties of a hardenable material can be modified through the addition of any of a variety of additives, such as carbon fibers, Kevlar or Titanium Rods, woven or laser etched metallic tubular stents, or other strength enhancers as will be understood in the art. The selection of a particular hardenable media, as well as the desirability of adding strength, flexibility, or other physical property enhancers, can be optimized for any particular implantation system through routine experimentation by those of skill in the art in view of the disclosure herein.
Certain composite materials, such as carbon fibers embedded in a bonding agent such as a two part epoxy, or two part polyurethane have been found particularly useful in forming the implant of the present invention. For example, graphite (carbon fibers) having a diameter within the range of from about 0.003 to about 0.007 inches are provided in bundles (tows) composed of from about 3,000 to about 12,000 fibers. One typical fiber useful for this purpose is manufactured by Hexcel Carbon Fibers, Salt Lake City, Utah, Part No. HS/CP-5000/IM7-GP 12K. Preferably, the Tow tensile strength is in the range of from about 5,000 to about 7,000 Mpa. Tow tensile modulus is within the range of from about 250 to about 350 Gpa.
In certain embodiments, the fixation rods are formed without the need of reinforcing fibers or rods. In such embodiments, the hardenable material itself exhibits physical properties sufficient for use in the implants.
In general, the composite rods in accordance with the present invention will exhibit a static compression bending values (per ASTM F1717) within the range of from about 100 to about 200 lbs., and, preferably greater than about 150 lbs. The composite rods will exhibit a static torsion (per ASTM F1717) within the range of from about 300 to about 500 inch pounds, and, generally in excess of about 400 inch pounds. The rods will preferably reach at least about 5 million cycles, at 5 Hz. Each of these parameters may be measured in accordance with the protocols described in the American Society for Testing and Materials (ASTM) designation F 1717-96, a copy of which is attached hereto as Appendix A, and which is incorporated in its entirety herein by reference.
Within the range of from about 30 to about 60 bundles of the carbon fiber described above is packed in a deflated balloon, optionally along with a Ni—Ti stent having an 8 mm diameter and 8 cm length. Although any of a variety of stents may be utilized, one useful structure is similar to the Smart Stent (Cordis), and it helps keep the structure intact and also adds structural strength to the implanted structure.
A one or a two part epoxy having a viscosity in the range of from about 100 to about 1000 cps is then injected into the balloon under pressure such as by using a pump and pressure within the range of from about 4 ATM to about 10 ATM or more depending upon viscosity, balloon strength and other design considerations. The pump is run for a sufficient duration and under a sufficient pressure to ensure that the epoxy wets all of the fibers. This may range from about 10 minutes or more to about an hour, and, in one application where the pump was run at about 5 ATM pressure, requires at least about ½ hour. Specific method parameters may be optimized depending upon the viscosity of the epoxy, infusion pressure, infusion flow rate, density of the packed carbon fibers, and other variables as will be apparent to those of skill in the art in view of the disclosure herein.
In an alternate embodiment, carbon fibers having within the range of from about 15 to about 45 degrees of braids are utilized. The braid may be in the form of a plain weave, and may be obtained, for example, from Composite Structures Technology (Tehachapi, Calif.). A 0.5 inch diameter of 45 degrees braided carbon fiber sleeve is positioned within the center of the balloon. This braided sleeve conforms dimensionally to the inside diameter of the balloon. A 0.3 inch diameter braided carbon sleeve (again 45°×45° plain weave) may also be positioned concentrically within the balloon, within the outer braided carbon fiber sleeve. Unidirectional fibers are thereafter introduced inside of the ID of the inner braided carbon sleeve. Unidirectional fibers are also introduced into the annular gap between the two braided sleeves. The volume of the fiber per volume of balloon is generally within the range of from about 40% to about 55%. After placement of the foregoing structure within the portals of the screws, the epoxy mix having a viscosity within the range of from about 100 to about 1000 cps is injected under 10 atmospheres pressure into the balloon.
Although the foregoing composite structure was described using a carbon fiber example, any of a variety of fibers may be positioned within the balloon to enhance the physical properties of the finished product. For example, Kevlar fibers, PEEK, and any of a variety of alternatives may be used. In general, the fibers will preferably provide a very high tensile strength and high modulus, having a low diameter to enhance deliverability of the device.
The use of braided sleeves will produce higher structural resistance to sheer stress as a result of torsional loads, plus the ability to distribute unidirectional fibers in a homogenous manner within the balloon at all times. This appears to improve the performance of the implant.
One construction of a composite formable rod in accordance with the present invention is illustrated in FIG. 4C. An outer balloon or other containment structure 114 is provided, as has been discussed. A reinforcing element 120 such as a stent is concentrically positioned within the balloon. An outer support tube 121 is positioned within the stent in the illustrated embodiment, however, the outer support tube 121 can alternatively be positioned concentrically outside of the stent 120. The outer support tube 121, in one embodiment, is a 0.5 inch diameter braided carbon fiber tube, having cross strands oriented at 45° angles with respect to each other to improve torsion resistance as has been discussed.
An inner support tube 123 is spaced radially inwardly from the outer support tube 121. Inner support tube 123, in one embodiment, comprises a 0.3″ diameter braided carbon fiber sleeve having characteristics described above. A first plurality of unidirectional fibers 125 is axially oriented within the annular space between the outer support tube 121 and inner support tube 123. A second plurality of unidirectional carbon fibers 127 is positioned within the inner support tube 123.
Any of a variety of alternate constructions can be readily utilized, in accordance with the teachings herein. For example, three or more tubular support tubes may be utilized. The layering sequence of the various components may be changed, and other features added or deleted depending upon the desired performance of the finished device. In addition, although the balloon 114 in one embodiment comprises a nylon single layer balloon, other materials may be utilized. In addition, multiple layer balloons may be utilized, with or without support structures such as stents, wires, or woven tubular support structures sandwiched therebetween.
In alternate embodiments, the formable rods do not include one or more of the reinforcing structures illustrated in FIG. 4C. In one such alternate embodiment, the first plurality of unidirectional fibers 125 and the second plurality of unidirectional fibers 127 are not present. In another such alternate embodiment, the inner support tube 123, outer support tube 121, and/or stent 120 are not present in the rod, which may or may not contain fibers 125, 127.
Other embodiments comprise a containment structure such as an outer balloon or mesh, and have none of the aforementioned reinforcing structures shown in FIG. 4C. In such other embodiments, the hardenable media alone suffices to form a rod having the needed strength and other physical characteristics. Embodiments that have few or no reinforcing or support structures are formed in substantially the same way as those discussed above, in that the hardenable media is injected into the containment structure in fluid form and then allowed to harden.
Marker bands made of materials such as gold, platinum or tantalum may also be positioned on the balloon, to facilitate fluoroscopic visualization. Alternatively, a radio opaque material, such as tantalum powder, may be sprinkled among the carbon fibers prior to infusion of the epoxy or other hardenable media, to allow visualization during placement.
The epoxy or the polyurethane material preferably has a relatively fast cure rate at 37° C. A low viscosity (no greater than from about 100 to about 1000 cps) facilitates rapid transluminal introduction through the delivery catheter and wetting of the relatively small interstitial spaces between adjacent carbon fibers. In addition, the polymer is preferably radiopaque. The polymerization is preferably minimally exothermic, to minimize or prevent thermal damage to the surrounding tissue. One epoxy which may be useful in the present invention is Epotek 301 available from Epoxy Technology, Inc. (Billerica, Mass.). This epoxy reaches 50 to 60% of its strength within about three to four hours following deployment, at 37° C. Using a bonding agent having these approximate characteristics, the patient can be restrained from rolling for an initial cure period of approximately three or four hours to achieve a partial cure (e.g., at least about 50% and preferably 60% or more), and be maintained in bed for a secondary cure period such as approximately the next eight to twelve hours or more to accommodate a full cure. Other formulations of two part epoxies or polyurethanes with faster cure times (preferably no more than about one hour full cure) can be formulated by changing the ratios of components and formulations for the catalysts. Cure time can also be accelerated through the use of accelerators, such as catalysts or the application of heat as is discussed in detail below.
In accordance with certain embodiments, preferred hardenable media have one or more of the following characteristics: (1) they cure completely at a temperature that approximates that of an animal body (about 35-42° C.); (2) they exhibit mildly exothermic curing behavior, meaning that the media only self-heats due to the curing reaction to a temperature below about 45° C., preferably below about 42° C. so as to reduce the risk of heat damage to nearby living tissues during curing; (3) they exhibit little or no shrinkage of during curing so as to maintain a tight fit following curing; (4) they have a pre-cure viscosity of preferably about 100-1000 cps, more preferably about 100-400 cps; (5) they have a useful life (“potlife”) (i.e. have a viscosity low enough to allow for injection) of no more than about 30 minutes after mixing/initiation/activation, preferably no more than about 15 minutes; (6) they are substantially cured (i.e. they are capable of forming a rigid rod of material) preferably within about 20-100 minutes or less, including within about 30, 40, 50, 60, 70, 80, and 90 minutes or less after initiation, such as by mixing; (7) they will form a substantially cured rod having a static compression bending value (per ASTM F1717) of at least about 60 lbs. (force), including about 70, 80, 90 and 100 lbs.; (8) they will form a fully cured rod (unreinforced) having static compression bending values (per ASTM F1717) within the range of from about 100 to about 200 lbs (force), preferably greater than about 150 lbs, including about 110, 120, 130, 140, 160, 170, 180, and 190 lbs., preferably within about 10-12 hours of initiation; (9) they will form a fully cured rod (unreinforced) having a static torsion (per ASTM F1717) within the range of from about 300 to about 500 inch pounds, preferably in excess of about 400 inch pounds; and (10) they will form a biocompatible solid. Especially preferred embodiments of hardenable media exhibit most or all of the foregoing characteristics.
One preferred family of hardenable media are two part epoxies having a very short cure time. The first part preferably comprises one or more compounds bearing epoxide groups, preferably two or more epoxide groups, and has a low viscosity. Preferred compounds include diepoxide resins having molecular weights between about 100 and 400, including, but not limited to, aromatic diepoxide compounds such as diglycidyl ether of Bisphenol A, and diglycidyl ether of Bisphenol F. Other preferred compounds include aliphatic epoxide resins, including cycloaliphatic resins. One preferred class of aliphatic epoxide resins are the diepoxide resins that are alkane diols of glycidyl ether, wherein the alkane portion is pentane, butane, propane, and the like. Such compounds generally have low viscosity (less than about 100 cp) and are sometimes called “reactive diluents” in that, when they blended with other epoxide materials, they serve to reduce the viscosity of the mixture as well as react to form cross-links within the matrix of the cured epoxy. The first part may also comprise monofunctional epoxide modifiers. In a preferred embodiment, the first part comprises a mixture of aromatic diepoxide compounds and aliphatic diepoxide compounds.
The second part preferably comprises one or more curing agents or hardeners, including, but not limited to, aliphatic and cycloaliphatic hardeners, mercaptan curing agents, and amine curing agents such as diamines, triamines, tetramines, methylamines, ethylamines, propylamines, aminopiperazines, and other specialty amines. Preferred curing agents or hardeners allow for cure of the media at ambient or near ambient temperatures, preferably below about 45° C. Preferred compounds include 1,3 diaminopropane, diethylenetriamine, triethylenetetramine, N-aminoethylpiperazine (including N-aminoethylpiperazine nonyl/phenol from Air Products and Chemicals, Allentown, Pa.) and compounds according to the general formula:
wherein each R is independently selected from branched or unbranched chains of about 2-10, preferably 2-5, carbon atoms, and x is 0, 1, or 2. In preferred embodiments, R is alkyl, preferably straight chained, and all R groups are the same. In some embodiments, the second part comprises a mixture of a cycloalkylamines, such as piperazine-based amines, and alkylamines.
In accordance with a preferred embodiment, formulations comprise about 60-80%, more preferably about 65-75% by weight of diepoxide compounds (first part) and about 20-40%, more preferably about 25-35% by weight of amine curing agent (second part). In one embodiment, the first part comprises about 45-52% by weight aromatic diepoxide compounds and about 19-23% by weight aliphatic diepoxide compounds, and the second part comprises about 20-29% alkyldiamines and about 4-9% by weight N-aminoalkylpiperazines. Five examples of formulations according to preferred embodiments are presented in Table 1 below.
Diglycidyl Ether of Bisphenol A
Butane Diol of Glycidyl Ether
Diglycidyl Ether of Bisphenol A
Butane Diol of Glycidyl Ether
Diglycidyl Ether of Bisphenol A
Butane Diol of Glycidyl Ether
Diglycidyl Ether of Bisphenol A
Butane Diol of Glycidyl Ether
Diglycidyl Ether of Bisphenol A
Butane Diol of Glycidyl Ether
For embodiments using other resins and/or hardeners, the amounts used will need to be adjusted to maintain the stoichiometric ratios (epoxy groups to amino groups), as will be appreciated by those skilled in the art.
The first part and/or the second part may further comprise a material to lend radiopacity or fluoropacity to the media so that it is more readily visualized during and after the procedure.
The hardenable material is made by mixing together the first and second parts. The first and second parts may be mixed prior to injection or they may be mixed during injection, such as by use of a static mixer as is known in the art. In preferred embodiments, the mixture is degassed to remove any air bubbles that are formed during mixing. Removal of air bubbles, if present, will serve to reduce the viscosity of the mixture and will also help prevent the formation of voids in the cured rod that result from air bubbles in the hardenable media.
Terms such as “hardenable” or “curable” media are used interchangeably herein, and are intended to include any material which can be transluminally introduced through the catheter body into the cavity 146 while in a first, flowable form, and transitionable into a second, hardened or polymerized form. These terms are intended to cover materials regardless of the mechanism of hardening. As will be understood by those of skill in the art, a variety of hardening or polymerizing mechanisms may exist, depending upon media selection, including hardening or polymerization due to exposure to UV or other wavelength of electromagnetic energy, catalyst initiated polymerization, thermally initiated polymerization, and the like. Mechanisms such as solvent volatilization may also be used, but are disfavored due to the greater likelihood of the formation of voids in the cured rod by evaporating solvent. While the media selection may affect catheter design in manners well understood by those of skill in the art, such as to accommodate outgassing of byproducts, application of heat, catalysts, or other initiating or accelerating influences, these variations do not depart from the concept of the invention of introducing a flowable media into a shape and subsequently curing the media to the shape. Two part media, such as a two part epoxy or polyurethane, or a monomer and an initiator may be introduced into the cavity 146 through separate lumen extending throughout the tubular body. Expandable media may also be provided, such as a material which is implantable in a first, reduced volume, and which is subsequently enlargeable to a second, enlarged volume such as by the application of water or heat, or the removal of a restraint.
A study was undertaken demonstrating the low exotherm during polymerization or hardening of a rod according to a preferred embodiment. The study involved the use of two pigs. In the first pig, 8 rods were implanted for mechanical strength studies. In the second pig, 5 rods were implanted for conducting thermal studies. All the rods were implanted in the back muscle near the vertebral structure. Epoxy formulation VL-14 mixed with tungsten powder (1-5 micron size) was injected at a pressure of about 8 atm (about 118 Psi) into the balloon to form the rod 2-3 minutes after it was mixed using an Angioplasty pump. Thermocouples were connected to the outside surface of the rods implanted in the second pig and a multichannel recorder connected to a PC monitored the temperature measured at the surface of the rod from the injection (time 0) to 60 minutes following injection at intervals of one minute. The data for one of the recorded channels is presented in FIG. 53. The data obtained for the other channels was substantially similar to that presented in the figure. As can be seen in
Various safety features to minimize the risk of rupture or leakage of the hardenable media may be utilized, depending upon design preferences. For example, a two-layer or three-layer or more balloon may be utilized to reduce the risk of rupture. In addition, the material of the single or multiple layers of the balloon may be selected to minimize escape of volatile components from the curable media. In one embodiment, a double balloon is provided having a nylon inside layer and a PET outside layer.
In addition, the inflation pressure of the curable media may be affected by the nature of the balloon. For example, a polyethylene balloon having a wall thickness of about 0.001″ may have a burst pressure of about 7 to 8 atmospheres. In that embodiment, an inflation pressure of no more than about 4 to 5 atmospheres may be desired. A slightly higher inflation pressure, such as on the order of from about 5 to about 6 atmospheres, may be utilized with a nylon balloon. Relatively noncompliant materials such as PET have much higher burst pressures (range of 10-20 atmospheres), as is well understood in the balloon angioplasty arts.
In addition, the balloon contains a proximal valve as will be discussed in additional detail below. Multiple valves may be utilized, in series along the flow path, to reduce the risk of failure and escape of hardenable media. As a further safety feature, the deployment catheter may be provided with an outer spill sheath in the form of an elongate flexible tubular body which surrounds the deployment catheter and at least a proximal portion of the balloon. This spill sheath provides an additional removable barrier between the junction of the catheter and the balloon, and the patient. If a spill occurs during the filling process, the spill sheath will retain any escaped hardenable media, and the entire assembly can be proximally retracted from the patient. Following a successful filling of the balloon, the spill sheath and deployment catheter can be proximally retracted from the patient, leaving the inflated formable orthopedic fixation structure in place.
The reinforcing element 120 may be exposed to the interior cavity 146 formed by the flexible wall 148, providing additional structural integrity. See, e.g.,
The reinforcement element 120 may include an expandable tubular stent. A stent of any suitable type or configuration may be provided with the delivery device, such as the Cordis artery stent (“smart stent”). Various kinds and types of stents are available in the market (Sulzer/Medica “Protege” stent and Bard “Memotherm” stent), and many different currently available stents are acceptable for use in the present invention, as well as new stents which may be developed in the future.
The balloon 114 may be removably attached to the tubular body 104 by a slip or friction fit on the distal end 108 of the outer sleeve 112 or on the inner sleeve 110. A variety of alternative releasable attachments may be used between the outer sleeve 112 and/or inner sleeve 110 and the proximal end 103 of the balloon 114, such as threaded engagement, bayonet mounts, quick twist engagements like a luer lock connector, and others known in the art. In each of these embodiments, a first retention surface or structure on the outer sleeve 112 and/or inner sleeve 110 releasably engages a complimentary surface or retention structure on the proximal end 103 of the balloon 114 as will be apparent to those of skill in the art.
The balloon 114 comprises a self-sealing valve 160 which prevents the hardenable media from leaking once the delivery catheter 100 is detached from the balloon 114. Valve 160 is provided for closing the pathway between inflation lumen 130 and inner cavity 146. Valve 160 may be located at the proximal end 116 of inflatable device 102. A variety of different valves may be used as will be recognized by those of skill in the art, such as a slit valve, check valve, duck-billed or flap valve. A pierceable, self-sealing septum may also be used. Alternatively, a stopper may be provided which can be placed within the pathway to prevent leakage.
An alternate valve is illustrated in
The valve 160 may be connected to or formed with the inflatable device in any of a variety of manners, as will be appreciated in view of the disclosure herein. In the illustrated embodiment, the balloon 114 is provided with a proximally extending neck 115 which carries the valve 160 therein. The tubular body 165 having the cap 167 thereon is positioned concentrically within the proximal neck 115, as illustrated in FIG. 4B. Alternatively, the valve 160 may be positioned within the balloon 114, i.e., distally of the proximal shoulder of the balloon 114.
Additional details of one detachable connection between the delivery system and the implantable device is illustrated in FIG. 4B. As illustrated therein, a tube 161 extends distally from the outer sleeve 112. Tube 161 may comprise any of a variety of materials, which exhibit sufficient structural integrity for the intended use. In one embodiment, tube 161 is a metal hypotube having an inside diameter of about 0.085″ to about 0.086 and a wall thickness of about 0.001″ to about 002″. The tube 161 in the illustrative embodiment extends for a distance of about 0.50 mm to about 0.75 mm beyond the distal end of the outer sleeve 112.
The tube 161 extends into a sliding fit with a tubular support structure 163 which may be positioned in a proximal neck portion of the balloon. When positioned as illustrated, the tube 161 ensures that the valve 160 is open, so that the inner sleeve 110 may extend axially therethrough into the balloon.
In addition, the inside diameter of the tube 161 is preferably sufficiently larger than the outside diameter of the inner sleeve 110 to provide an annular passageway in communication with the vent lumen 132. This structure ensures that the interior of the balloon remains in communication with the proximal vent port by way of a vent lumen 132 extending throughout the length of the assembly. In the illustrated embodiment, the outside diameter of the inner sleeve 110 is about 0.082″ to about 0.084″, and the inside diameter of the tube 161 is about 0.085″ to about 0.086″. Following infusion of the curable media into the balloon, the inner tube 110 and tubular body 161 are both proximally retracted from the balloon, thereby enabling the valve 160 to close as is described elsewhere herein.
When fully inflated, as shown in
The bone anchors of
Bone anchor 10 comprises a proximal portion 12 having a proximal end 14 and a distal portion 16 having a distal end 18. Proximal portion 12 typically comprises a head 20 and a portal 22. In a preferred embodiment, head 20 comprises a proximal portion 24 configured to mate with the tip of a screwdriver. Head 20 may comprise a standard or Phillips slot for mating with the screwdriver. A variety of slot configurations are also suitable, such as hexagonal, Torx, rectangular, triangular, curved, or any other suitable shape. The bone anchor of
Portal 22 of bone anchor 10 may extend through head 20 and is generally between about 4 mm and 8 mm in diameter, preferably about 6 mm to about 8 mm in diameter. Portal 22 may be of any shape suitable for receiving inflatable, implantable orthopedic device 102; however, portal 22 is preferably round.
Distal portion 16 of bone anchor 10 typically comprises threads 26 and a sharp tip 28. Bone anchor 10 also preferably comprises a central lumen 30 extending coaxially completely through bone anchor 10 from proximal end 14 to distal end 18 and configured to receive a guidewire. Bone anchor 10 may also include at least one perforation 32, as shown in FIG. 13. Perforation 32 may be aligned axially, as shown, or may be staggered axially. Perforation 32 permits bone to grow into bone anchor 10, stabilizing bone anchor 10 within the bone. Additionally, bone matrix material such as a hydroxyapatite preparation can be injected into central lumen 30 and through perforation 32 to promote bone in-growth.
Distal portion 46 comprises a shaft 52 having a tip 54 configured to interface with proximal portion of bone anchor 10. Screwdriver 40 may also comprise a central lumen 55 extending coaxially from proximal end 44 to distal end 48 configured to receive a guidewire.
A directing sheath 180, as shown in
Directing sheath 180 is preferably formed from a biocompatible polymer. Directing sheath 180 may also include a radiopaque filament 194 passing around each opening in central portion 186 or the entire length of sheath 180. Filament 194 aids in localizing directing sheath 180 after percutaneous placement.
The accelerator is not necessary a part of the delivery catheter 100.
In order to accomplish the objective of accelerating polymerization of the epoxy or other hardenable media, the heating element preferably elevates the temperature of the epoxy to a point above normal body temperature. Temperatures at the heating element of at least about 43°, preferably at least about 50°, and, under certain circumstances as high as 60° C. or more are desirable to produce an optimal cure rate. However, the outside of the implant is preferably not heated to the extent that it causes localized tissue necrosis. Tissue necrosis occurs at approximately 45° C. Thus, the heat source preferably sets up a temperature differential between the surface of the implant and the interior of the implant. This may be accomplished in several ways, such as, for example, selecting materials and thickness of the outer flexible wall 148 to provide thermal insulation of the adjacent tissue from heat generated by the heating element. As an alternative or in addition, heat sink structures may be provided at or near the outer surface of the orthopedic device 102. A flow path such as an annular space formed within a double walled balloon may be utilized to circulate a coolant such as saline or other circulating cooling fluid. Such measures preferably permit the heating element to be heated as high as 50° C. or higher, while maintaining the outside surface of the device 102 at a temperature of no more than about 45° C., and, preferably no more than about 43° C.
Excessive temperature can also be reached transiently, such as at the beginning of a heating cycle when the temperature may temporarily overshoot the 45° C. desired maximum. The present inventors have determined that the initial temperature overshoot can be eliminated or reduced by appropriately driving the power to the heating element as is discussed in detail below. The driver circuitry preferably brings the heating element up to operating temperature rapidly, while minimizing the risk of thermal overshoot beyond a predetermined maximum. All of the foregoing measures preferably allow a sufficient curing of the hardenable media to limit the required period of immobility to no more than about 2 hours, preferably no more than about 1 hour and, optimally no more than about 45 minutes post implantation. Although a complete cure is not required within this time window, a sufficient cure is desirable that the patient need not be immobilized beyond the initial cure. Thereafter, the hardenable media will continue to harden, such as over the next few hours or even days, but with little or no restriction on the patient's activities.
The resistive heating element, whether the heating coil 300, the reinforcement element 120, or other structure, may be made from material with either a positive or negative temperature coefficient of resistance, e.g., electrical resistance either directly or indirectly proportionate to temperature, respectively. The temperature may be monitored by measuring the DC voltage across the resistive heating element, for the voltage is directly proportional to resistance for a given current, and the temperature coefficient of resistance is known. Alternatively, by measuring the voltage, current and phase of the drive system, the resistance of the heating element and thus its temperature can be calculated by a microprocessor or dedicated circuitry.
Alternatively a thermistor 314 may be used to monitor the temperature of the inflatable orthopedic device 102. Thermistors are well known in the art. Using one or more separate thermistors 314 would entail more electrical contacts (not shown) as another electrical loop in addition to the one running the heating element may be necessary. Other methods of measuring the temperature include the use of an optical fiber in conjunction with a thermally reactive material, a coaxial plunger in conjunction with a thermal bulb, or a semiconductor temperature sensor or junction (such as a diode) carried by the orthopedic implant. A bimetallic heating element may function similarly to a circuit breaker and self-regulate.
The illustrated embodiment of the control panel 316 has a cycle button 600 with which to select the heating cycle, and a cycle window 602 to display the cycle selected. The control panel 316 is also provided with a pause switch 604 to pause the heating cycle, and LED's 606 and 608 respectively to indicate whether the cycle is running or paused. A time window 610 indicates the time elapsed in the heating cycle. An optional toggle switch (not shown) may be used to toggle the time window 610 to display the time remaining in the heating cycle. A power switch 612 turns the control panel on and off while a power LED 614 displays its power status. A heating LED 616 indicates whether the heating cycle is in a heating phase. Warning LED's 618 indicate whether there is a fault in the circuitry or connection with the heating element 300. Battery LED's indicate the charge status of the battery.
Low-pass filters 332 isolate the high frequency power generator 326 from a precision current source 334 and an amplifier 336. The precision current source 334 feeds a low precise DC current through the heating element 330. The resulting DC voltage across the heating element 330 is amplified by the amplifier 336 and compared against a reference voltage generated by a reference module 338. The comparison is done by a level comparator 340. As voltage is directly proportionate to resistance at a given current, the resistance across the heating element 330 can thus be measured. With the temperature coefficient of resistance of the heating element 330, the temperature of the heating element 330 can thus be calculated. The control block 324 acts on feedback from the comparator 340 to enable or disable the high frequency power generator 326, and thus regulate the temperature of the heating element 330 according to the heating profile. In one embodiment a clinical practitioner may have the option of overriding the heating profile by inputting the desired temperature into the control block 324 directly. While a resistive heat source has been described in some of the above embodiments, other energy sources to accelerate the curing of the curable media may be used. These include, but are not limited to, adding a polymerizing agent, radio frequency, ultrasound, microwave and lasers. Also, the complete curing of the curable media by the described apparatus and methods is not always required to occur before discontinuing the heat source or other initiator step in these embodiments. When the curable media has been partially cured to a certain level of structural integrity, the patient does not have to be retrained for the remaining cure time necessary to achieve a complete cure. Thus the period of patient immobilization is minimized using the curing accelerators of the present invention.
Another specific embodiment is described in connection with
The inner electrical connector tube 438 is coaxially carried by the exterior perimeter of the suction tube 434. The outer electrical connector tube 440 is coaxially arranged around the exterior perimeter of the inner electrical connector tube 438. A layer of electrical insulation is provided between the two electrical connector tubes 438 and 440. This can be accomplished by coating the inner surface of the outer electrical connector tube 440 or the outer surface of a proximal portion of the inner electrical connector tube 438 with an electrically insulating material, such as polyurethane or PTFE. Both electrical connector tubes 438 and 440 may be slotted to ease connection, as discussed below. A wire connects each electrical connector tube to the drive circuit of the heating element 408. Each electrical connector tube may have an additional wire connected to it, which may be used together as a dedicated feedback loop to more accurately measure the electrical resistance of the heating element 408. A spacer tube 442 is provided with a notch 443 which provides an annular seat for the proximal end of the outer electrical connector 440, to hold the outer electrical connector tube 440 in place.
A lock tube 444 is coaxially arranged around the exterior perimeter of the spacer tube 442. The lock tube 444 is provided with one or two or more axially extending slits 445 and provided with a radially inwardly extending projection 446 for releasable engagement with a corresponding annular recess on the proximal end of the balloon 400, as discussed below. The inner tube 448 holds the suction tube 434 and the injection tube 430, as all three extend all the way proximally into the catheter handle. The outer tube 450 terminates proximally at a luer lock at the distal end of the catheter handle.
When the catheter is attached to the balloon 400, the inner electrical connector tube 438 contacts the inner electrical connector ring 422, and the outer electrical connector tube 440 contacts the outer electrical connector ring 424. As described above, both electrical connector tubes are slotted to ease their insertion into the respective electrical connector rings. These two contacts complete the electric circuit between the heating element 408 and its drive circuitry.
The lock tube 444 holds the balloon 400 in place at the end of the catheter. A seal 426 at the proximal end 416 of the balloon 400 seals against the interior surface of the lock tube 444. As described above, the lock tube 444 is slit to ease its insertion over the proximal end 416 of the balloon 400. One or more radially inwardly extending projections 446 provided on the interior surface of the lock tube 444 complements the bottleneck 428 in the proximal end 416 of the balloon 400 to provide an interference engagement which is maintained by the outer tube 450. The outer tube 450 may be released via the luer lock 506, allowing it to slide distally over the lock tube 444 to restrain the projection 446 of the lock tube 444 within the bottleneck 428 of the balloon 400.
Any of a variety of releasable connectors may be utilized, between the catheter and the implant. For example, threaded connections, twist locks, interference fit and friction fit structures are well known in the art. In general, a releasable connection which will withstand sufficient tension and compression during the positioning process is preferred. Such structures will generally include an interference fit. In the illustrated embodiment, a radially inwardly extending annular ridge which is provided with two or more axially extending slots to allow lateral movement cooperates with a radially inwardly extending annular recess on the proximal end of the implant as has been discussed. The radially inwardly extending ridge provides an interference surface, which may also be carried by one or more lever arms or other support structures. The relationship may alternatively be reversed between the deployment catheter and the implant, such that one or more radially outwardly extending projections on the implant engage a radially outwardly extending recess on the interior wall of the deployment catheter. In general, a positive interference fit can be readily accomplished by a first locking surface on the catheter which is removably engaged with a second, complementary locking structure on the implant. Preferably, one of the first and second locking structures is laterally moveable to engage and disengage the implant, and a lock is provided for releasably locking the first and second engagement surfaces to releasably retain the implant on the catheter.
The deployment and release of the inflatable orthopedic balloon 400 is now described. A guide wire may be inserted into the injection lumen 432 to stiffen the entire catheter to facilitate insertion of the balloon 400. This guide wire may be inserted via the injection port 502. Ideally this guide wire extends all the way to the distal end 402 of the balloon, and has a diameter that permits axial movement within the inner diameter of the injection tube 430. The insertion of the balloon 400 may be visualized by fluoroscopy of the distal marker 404 and the proximal marker 418. The guide wire is removed prior to the injection of curable medium into the balloon 400 via the injection lumen 432.
The injection port 502 is then connected to a pump, which pumps curable medium into the balloon 400 through the injection tube 430. As the injection tube 430 in the illustrated embodiment extends through the inner tubing 406 into or close to the distal end 402 of the balloon 400, the balloon is filled from the distal end 402 first. A vacuum is connected to suction port 504. As described above, the suction tube 434 extends through the valve assembly 420 of the balloon 400 to a point just distal of the proximal marker 418, and the inner tubing 406 of the balloon 400 is porous. This suction thus contributes to the filling of the balloon 400 with curable medium.
After the space 412 (as defined by the volume between the inner tubing 406 and the outer wall 414 of the balloon 400) is filled with curable medium, the luer lock 510 may be disengaged to allow the removal of the injection tube 430 and the suction tube 434. Any space remaining in the inner tubing 406 is filled with curable medium as the injection tube 430 is slowly pulled out. The valve assembly 420 of the balloon 400 prevents any curable medium from leaking.
For those embodiments in which heating is used to accelerate the curing of the hardenable media, a high frequency current is passed through the heating element 408 to accelerate the curing of the curable medium in the balloon 400, as has been discussed above in FIG. 47.
After the completion of the heating cycle (if performed), the catheter is removed from the balloon 400 by first sliding outer tube 450 proximally, exposing the lock tube 444. As described above, the lock tube 444 is slit. Without the outer tube 450 around it, the rounded proximal surface of projection 446 of the lock tube 444 will slide over and off the bottleneck 428 of the balloon 400 as the catheter handle 500 is pulled proximally. This action will also disengage the inner electrical connector tube 438 from the inner electrical connector ring 422 and the outer electrical connector tube 440 from the outer electrical connector ring 424. The balloon 400 is thus left in place after the removal of the catheter.
Although the application of the present invention will be disclosed in connection with connecting two adjacent vertebrae, the methods and structures disclosed herein are intended for various other applications such as to connect three or more vertebrae, as will be apparent to those of skill in the art in view of the disclosure herein. In addition, the method may be used to stabilize the L5 vertebrae, using the cranial-ward portion of the sacrum as the vertebrae with which L5 is anchored. Furthermore, although the method is disclosed and depicted as applied on the left side of the vertebral column, the method can also be applied on the right side of the vertebral column, or both sides of the vertebral column sequentially or simultaneously.
The method of the present invention involves percutaneously inserting one or more fusion devices into two or more than two adjacent vertebrae, either unilaterally or, preferably bilaterally, where a portion or all of at least one of the vertebrae is unstable, separated or displaced. The fusion devices reposition or fix the displaced vertebra or portion of the displaced vertebra to a position within the vertebral column which is more stable or which causes less morbidity.
Referring now to FIG. 18 through
The method will now be disclosed and depicted with reference to only two vertebrae, one which is either unstable, separated or displaced and one of which is neither unstable, separated nor displaced. However, the method can also be applied to three or more vertebrae simultaneously, as will be understood by those with skill in the art with reference to this disclosure. Additionally, the method can be used to stabilize the L5 vertebrae, using the cranial-ward portion of the sacrum as the “vertebrae” with which L5 is anchored. Further, though the method is disclosed and depicted as applied on the left side of the vertebral column, the method can also be applied on the right side of the vertebral column or, preferably, can be applied on both sides of the vertebral column, as will be understood by those with skill in the art with reference to this disclosure.
First, the present method comprises identifying a patient who is a suitable candidate for undergoing the method. In connection with a spinal application, a suitable candidate has one or more unstable vertebrae, one or more portions of one or more vertebrae at least partly separated from the remainder of the vertebrae, one or more portions of one or more vertebrae at least partly separated from the remainder of the vertebrae with potential or complete separation, or has one or more vertebrae or a portion of one or more vertebrae displaced from its normal position relative to the vertebral column, or has one or more portions of one or more vertebrae at least partly separated from the remainder of the vertebrae and displaced from its normal position relative to the vertebral column. Further, the suitable candidate will normally have either pain, loss of function or real or potential instability which is likely due to the separation or displacement, or separation and displacement. If only a portion of the vertebra is unstable, separated or displaced, the portion of the vertebra that is unstable, separated or displaced will generally include at least part of the vertebral body and adjoining pedicle. However, other unstable, separated or displaced portions of a vertebra can be repositioned or fixed using the present method, as will be understood by those with skill in the art with reference to this disclosure. For example, a suitable patient can have a disease or condition such as spondylosis, spondylolisthesis, vertebral instability, spinal stenosis and degenerated, herniated, or degenerated and herniated intervertebral discs, though actual indications require the expertise of one of skill in the art as will be understood by those with skill in the art with reference to this disclosure.
Next, the present method comprises making a stab incision in the patient's skin overlying the patient's vertebral column at or near the level of the vertebrae or portion of vertebrae to be repositioned or fixed. In one embodiment, the incision is made at or near the level of the pedicle of the vertebra or portion of vertebra to be repositioned or fixed. The pedicle level is located preferably by identifying the pedicle shadow using fluoroscopy. In a preferred embodiment, the stab incision is made using a #11 scalpel blade.
Then, as shown in
Then, as shown in
The biopsy needle 202 is then removed and the tract from the skin surface to the nicked periosteal surface is enlarged by using a high-pressure fascial dilator balloon (not shown) over the needle-tipped guidewire. Then, the balloon is removed and a working sheath 206 is introduced into the dilated tract. Alternately, a hard plastic or metallic sheath with a central dilator is advanced over the guidewire from the skin surface to the periosteal surface. Next, a pilot hole may be drilled using an over-the-wire drill bit driven by a hand held drill.
Next, as shown in
The stages discussed above are repeated for at least one additional vertebra 212 until each vertebra that is to be repositioned or fixed has a bone screw 208 applied, and additionally for at least one vertebra which is neither unstable, separated nor displaced and which lies adjacent the cranial-most or caudal-most vertebra that is being repositioned or fixed. The bone screw 208 placed into the vertebra 212 which is neither unstable, separated nor displaced is used as the anchor to reposition or fix each vertebra 200 which is unstable, separated or displaced as follows. As will be understood by those with skill in the art with reference to this disclosure, the bone screws can be placed into the vertebrae in a different order to that described above.
After a bone screw is positioned in each vertebra, the portals are connected using an inflatable connection rod according to the present invention where the rod is inserted between the portals of the bone screws and inflated to create a rigid structure with the bone screws, thereby repositioning and fixing the one or more than one previously unstable, separated or displaced vertebra, or one or more previously unstable, separated or displaced portions of one or more vertebrae with the vertebra that is neither unstable, separated nor displaced. Connection of the bone screws with the inflatable rod is accomplished as follows.
Referring now to FIG. 22 and
Then, as shown in
In one embodiment, as further shown in
In another embodiment, as further shown in
In another embodiment, the needle-tipped, semi-rigid guidewire 216 comprises an outer helical, flat wire sheath and an inner retractable sharp tip stylet. Once the needle-tipped, semi-rigid guidewire is placed, the stylet can be removed to allow for easier capture by the capture device with less trauma to the surrounding tissue.
Then, as shown in
Next, as shown in
Then, as shown in
Finally, as shown in
Referring now to
In another embodiment of the present method, a directing sheath 180 according to the present invention is advanced over a guidewire until the openings in the directing sheath 180 overlie the position in each vertebra which will receive a bone screw 208. The bone screws 208 are then placed as disclosed in this disclosure, but through the openings in the directing sheath 180, which aligns the lumen in the directing sheath with the portals of the bone screw 208. Then (not shown), a guidewire is inserted into the lumen of the directing sheath at the proximal end of the directing sheath and advanced until the guidewire passes through each portal of the bone screws and exits the body through the lumen of the directing sheath at the distal end. The directing sheath is then removed by peeling the sheath apart along the scored lines and pulling the two halves out from the body. The guidewire that was in the lumen of the directing sheath remains in place to guide the placement of the uninflated, inflatable connection rod. Alternately, the uninflated, connection rod can be inserted directly into the lumen of the directing sheath at the proximal end and advanced until the uninflated, inflatable connection rod is properly positioned between the portals of the bone screws. Referring now to
In one embodiment, there is provided a kit for performing methods of the present invention. The kit comprises a plurality of bone screws according to the present invention. The kit can also comprise other components of the system of the present invention, such as a guidewire directing device, an inflatable connection rod, the curable medium to be injected and a directing sheath. The curable medium may comprise one part or it may comprise two or more parts that are mixed before, during or after injection. In another preferred embodiment, the kit also comprises a screwdriver according to the present invention. A control with electronic driving circuitry can also be provided, for thermal acceleration of the hardenable media.
Cross-linking may be accomplished in any of a variety of configurations, as will be apparent to those of skill in the art in view of the disclosure herein. For example, a pair of laterally opposing pedicle screws 208 may be connected to each other by an inflatable crossbar or solid crossbar as will be apparent from the disclosure herein. Alternatively, the body of the two opposing inflatable connection rods 222 a and 222 b can also be connected by a crossbar. Although the present discussion will focus primarily upon the latter construction, it is to be understood that the present invention contemplates any cross connection between a left and right connection rod, preferably through a procedure in which each of the connection rods or crossbars is installed in a less invasive or minimally invasive procedure.
A cross tie support 248 is axially movably positioned within the access sheath 232. Cross tie support 248 is connected at a distal end 249 through a releasable connector 246 to a cross tie 234. Cross tie 234 facilitates connection of a crossbar with a primary inflatable connection rod, to achieve cross linking of the orthopedic fixation system.
Although a variety of structures for cross tie 234 can be utilized, one convenient construction is illustrated in FIG. 37. In general, the cross tie 234 includes a first connector 236 such as a first aperture 238 for receiving an inflatable connection rod 222 as has been discussed previously herein. In one implementation, the aperture 238 has an inside diameter of approximately 6 mm. However, diameters of the first aperture 238 may be varied widely, depending upon the diameter of the inflatable connection rod 222, and the desired physical performance characteristics.
The cross tie 234 additionally comprises a second connector 240, such as a second aperture 242. The second aperture 242 is adapted to receive a crossbar 222 c, as illustrated in
The cross tie 234 is held in place during the procedure by a cross tie support 248 through a releasable connector 246. The releasable connector 246 facilitates the positioning of the cross tie 234 during the deployment step, but enables decoupling following proper positioning of at least an inflatable connection rod 222 a and possibly also the crossbar 222 c. Any of a variety of releasable connection structures may be utilized, such as a threaded distal end on the cross tie support 248, which threadably engages an aperture on the cross tie 234.
As illustrated in
Preferably, the first aperture 238 is dimensioned with respect to the connection rod 222 a such that a secure fit is provided between the inflatable connection rod 222 a and cross tie 234 following complete curing of the curable media. If shrinkage of the curable media is contemplated, the first aperture 238 may be defined within an annular ring on the frame 244 which has an expansion break extending therethrough. In this manner, inflation of the inflatable connection rod 222 a can be accomplished such that the expansion break allows a slight enlargement of the diameter of the first aperture 238. Upon transverse shrinkage of the inflatable connection rod 222 a during the curing process, the natural bias imparted by the frame 244 allows the first aperture 238 to shrink, thereby retaining a tight fit with the inflatable connection rod 222 a throughout a range of diameters. This construction may also be applied to the apertures extending through the bone screws 208, as well as the second apertures 242.
The cross tie support 248 is illustrated in
The final construction is illustrated in FIG. 35. As seen therein, a crossbar 222 c extends between a first cross tie 234 carried by the first inflatable connection rod 222 a and a second cross tie 234 carried by the second inflatable connection rod 222 b. The crossbar 222 c may be positioned through the pair of opposing apertures 242 using the same techniques discussed and illustrated previously herein for the implantation of the inflatable connection rods 222. The initial position of a curved needle and guidewire for positioning the crossbar 222 c is schematically illustrated in FIG. 36.
Although only a single crossbar 222 c is illustrated, two or three or four or more crossbars 222 c may alternatively be used, depending upon the axial lengths of the inflatable connection rods 222 a and 222 b, and the desired structural integrity of the finished assembly. In addition, although the crossbar 222 c is illustrated as extending generally perpendicular to the longitudinal axis of each of the inflatable connection rods 222 a and 222 b, the crossbar 222 c may cross each of the inflatable connection rods 222 at any of a variety of angles ranging from approximately +45° to −45° with respect to the illustrated position. Thus, the crossbar 222 c may be implanted at a diagonal if the desired structural integrity can be thus achieved.
The crossbar 222 c may comprise any of a variety of forms. For example, the crossbar illustrated in
In an alternate application of the cross-linking technology of the present invention, the crossbar is constructed in a manner which enables elimination of the separate cross tie 234. Referring to
The 21 French dilator 260 is advanced over a stiff 0.038″ guidewire, with an 8 French catheter. A 24 French pusher sheath 262 is positioned proximally of the tubular body 254.
Using this deployment system, the tubular body 254 may be positioned relative to two pairs of bone screws 208 as illustrated schematically in
The tubular body 254 may by itself provide sufficient cross-linking strength for the intended purpose. Alternatively, the tubular body 254 may be filled with a curable media 266 to enhance the structural integrity of the resulting assembly. For example, as illustrated in
The embodiment of
The various materials, methods and techniques described above provide a number of ways to carry out the invention. Of course, it is to be understood that not necessarily all objectives or advantages described may be achieved in accordance with any particular embodiment described herein. Thus, for example, those skilled in the art will recognize that the materials such as media may be made and the methods may be performed in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other objectives or advantages as may be taught or suggested herein.
Although the present invention has been described in terms of certain preferred embodiments, other embodiments of the invention including variations in dimensions, configuration and materials will be apparent to those of skill in the art in view of the disclosure herein. In addition, all features discussed in connection with any one embodiment herein can be readily adapted for use in other embodiments herein. The use of different terms or reference numerals for similar features in different embodiments does not imply differences other than those which may be expressly set forth. Accordingly, the present invention is intended to be described solely by reference to the appended claims, and not limited to the preferred embodiments disclosed herein.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2267625||Mar 4, 1940||Dec 23, 1941||Samuel Wulfson||Container for tooth paste|
|US3834384||May 1, 1973||Sep 10, 1974||Raines H||Surgical mask with adhesive vapor barrier|
|US4041939||Apr 26, 1976||Aug 16, 1977||Downs Surgical Limited||Surgical implant spinal screw|
|US4327734||Sep 29, 1980||May 4, 1982||White Jr Robert I||Therapeutic method of use for miniature detachable balloon catheter|
|US4341218||Mar 6, 1980||Jul 27, 1982||University Of California||Detachable balloon catheter|
|US4364392||Dec 4, 1980||Dec 21, 1982||Wisconsin Alumni Research Foundation||Detachable balloon catheter|
|US4383879||Mar 20, 1981||May 17, 1983||Commissariat A L'energie Atomique||Cement for the fixation of osseous prostheses|
|US4441495||Aug 16, 1982||Apr 10, 1984||Becton, Dickinson And Company||Detachable balloon catheter device and method of use|
|US4517979||Jul 14, 1983||May 21, 1985||Cordis Corporation||Detachable balloon catheter|
|US4545367||Nov 18, 1983||Oct 8, 1985||Cordis Corporation||Detachable balloon catheter and method of use|
|US4743260||Jun 10, 1985||May 10, 1988||Burton Charles V||Method for a flexible stabilization system for a vertebral column|
|US4904260||Jul 25, 1988||Feb 27, 1990||Cedar Surgical, Inc.||Prosthetic disc containing therapeutic material|
|US5139499||Sep 5, 1990||Aug 18, 1992||American Cyanamid Company||Screw and driver|
|US5146933||Sep 20, 1991||Sep 15, 1992||Dow Corning Wright Corporation||Implantable prosthetic device and tethered inflation valve for volume|
|US5165919||Mar 15, 1989||Nov 24, 1992||Terumo Kabushiki Kaisha||Medical material containing covalently bound heparin and process for its production|
|US5171279||Mar 17, 1992||Dec 15, 1992||Danek Medical||Method for subcutaneous suprafascial pedicular internal fixation|
|US5181921||May 24, 1991||Jan 26, 1993||Kaken Co., Ltd.||Detachable balloon with two self-sealing valves|
|US5222970||Sep 6, 1991||Jun 29, 1993||William A. Cook Australia Pty. Ltd.||Method of and system for mounting a vascular occlusion balloon on a delivery catheter|
|US5242443||Aug 15, 1991||Sep 7, 1993||Smith & Nephew Dyonics, Inc.||Percutaneous fixation of vertebrae|
|US5242444||Nov 4, 1991||Sep 7, 1993||University Of Florida||Lumbosacral fixation and fusion method and device|
|US5357983||Jan 4, 1993||Oct 25, 1994||Danek Medical, Inc.||Method for subcutaneous suprafascial pedicular internal fixation|
|US5496322||Jul 22, 1994||Mar 5, 1996||Danek Medical Inc.||Method for subcutaneous suprafascial pedicular internal fixation|
|US5529653||Mar 20, 1995||Jun 25, 1996||Industrial Research B.V.||Expandable hollow sleeve for the local support and/or reinforcement of a body vessel, and method for the fabrication thereof|
|US5549679||Mar 1, 1995||Aug 27, 1996||Kuslich; Stephen D.||Expandable fabric implant for stabilizing the spinal motion segment|
|US5571189||May 20, 1994||Nov 5, 1996||Kuslich; Stephen D.||Expandable fabric implant for stabilizing the spinal motion segment|
|US5584887||Oct 23, 1992||Dec 17, 1996||Smith & Nephew Richards, Inc.||Percutaneous screw adapter|
|US5591199||Jun 7, 1995||Jan 7, 1997||Porter; Christopher H.||Curable fiber composite stent and delivery system|
|US5593408||Nov 30, 1994||Jan 14, 1997||Sofamor S.N.C||Vertebral instrumentation rod|
|US5658286||Feb 5, 1996||Aug 19, 1997||Sava; Garard A.||Fabrication of implantable bone fixation elements|
|US5728097||Jul 9, 1996||Mar 17, 1998||Sdgi Holding, Inc.||Method for subcutaneous suprafascial internal fixation|
|US5772661||Feb 27, 1995||Jun 30, 1998||Michelson; Gary Karlin||Methods and instrumentation for the surgical correction of human thoracic and lumbar spinal disease from the antero-lateral aspect of the spine|
|US5779672||Mar 5, 1997||Jul 14, 1998||Interventional Therapeutics Corporation||Dual valve detachable occlusion balloon and over-the-wire delivery apparatus and method for use therewith|
|US5792044||Mar 22, 1996||Aug 11, 1998||Danek Medical, Inc.||Devices and methods for percutaneous surgery|
|US5795353||Nov 2, 1996||Aug 18, 1998||Advanced Bio Surfaces, Inc.||Joint resurfacing system|
|US5800435||May 1, 1997||Sep 1, 1998||Techsys, Llc||Modular spinal plate for use with modular polyaxial locking pedicle screws|
|US5827289||Jun 5, 1996||Oct 27, 1998||Reiley; Mark A.||Inflatable device for use in surgical protocols relating to treatment of fractured or diseased bones|
|US5888220||Jan 23, 1996||Mar 30, 1999||Advanced Bio Surfaces, Inc.||Articulating joint repair|
|US5899939||Jan 21, 1998||May 4, 1999||Osteotech, Inc.||Bone-derived implant for load-supporting applications|
|US5972015||Aug 15, 1997||Oct 26, 1999||Kyphon Inc.||Expandable, asymetric structures for deployment in interior body regions|
|US5980253||Jan 12, 1998||Nov 9, 1999||3M Innovative Properties Company||Process for treating hard tissues|
|US6025406||Apr 11, 1997||Feb 15, 2000||3M Innovative Properties Company||Ternary photoinitiator system for curing of epoxy resins|
|US6033406||Mar 17, 1998||Mar 7, 2000||Sdgi Holdings, Inc.||Method for subcutaneous suprafascial pedicular internal fixation|
|US6042380||Nov 25, 1998||Mar 28, 2000||Discotech Medical Technologies, Ltd.||Inflatable dental implant for receipt and support of a dental prosthesis|
|US6043295||Jul 28, 1999||Mar 28, 2000||3M Innovative Properties Company||Ternary photoinitiator system for curing of epoxy resins|
|US6048346||Aug 13, 1997||Apr 11, 2000||Kyphon Inc.||Systems and methods for injecting flowable materials into bones|
|US6066154||Jan 22, 1997||May 23, 2000||Kyphon Inc.||Inflatable device for use in surgical protocol relating to fixation of bone|
|US6080801||Jul 14, 1998||Jun 27, 2000||Klaus Draenert||Multi-component material and process for its preparation|
|US6099528||May 28, 1998||Aug 8, 2000||Sofamor S.N.C.||Vertebral rod for spinal osteosynthesis instrumentation and osteosynthesis instrumentation, including said rod|
|US6126689||Jul 9, 1999||Oct 3, 2000||Expanding Concepts, L.L.C.||Collapsible and expandable interbody fusion device|
|US6127597||Mar 6, 1998||Oct 3, 2000||Discotech N.V.||Systems for percutaneous bone and spinal stabilization, fixation and repair|
|US6149655||Dec 12, 1997||Nov 21, 2000||Norian Corporation||Methods and devices for the preparation, storage and administration of calcium phosphate cements|
|US6159012||Sep 1, 1999||Dec 12, 2000||3M Innovative Properties Company||Process for treating hard tissues|
|US6175758||Aug 9, 1999||Jan 16, 2001||Parviz Kambin||Method for percutaneous arthroscopic disc removal, bone biopsy and fixation of the vertebrae|
|US6235028||Feb 14, 2000||May 22, 2001||Sdgi Holdings, Inc.||Surgical guide rod|
|US20020068975||Oct 10, 2001||Jun 6, 2002||Teitelbaum George P.||Formable orthopedic fixation system with cross linking|
|US20020082598||Dec 21, 2000||Jun 27, 2002||Teitelbaum George P.||Percutaneous vertebral fusion system|
|US20020082600||Aug 29, 2001||Jun 27, 2002||Shaolian Samuel M.||Formable orthopedic fixation system|
|1||Bennett, Gregory J., Lumbosacral Stabilization Using Screw Fixation Techniques, Neurosurgery, McGraw-Hill Health Professions Division, Second Edition, vol. II, pp. 3027-3035.|
|2||Kyphon Inc., Kypohon; Fragility Fracture Management: About Kypon, 2000.|
|3||Müller, Adolf, M.D. et al. A Keyhole Approach for Endoscopically Assisted Pedicle Screw Fixation in Lumbar Spine Instability, Neurosurgery, vol. 47, No. 1, Jul. 2000, pp. 85-98.|
|4||Wilkins, Robert H., M.D. et al. Neurosurgery 2<nd >Edition, vol. 1, pp. 3027-3035.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7651496||Jul 19, 2005||Jan 26, 2010||Zimmer Spine, Inc.||Methods and apparatuses for percutaneous implant delivery|
|US7655026 *||Jan 31, 2006||Feb 2, 2010||Warsaw Orthopedic, Inc.||Expandable spinal rods and methods of use|
|US7686809||Jan 9, 2007||Mar 30, 2010||Stryker Spine||Rod inserter and rod with reduced diameter end|
|US7695499||Apr 29, 2005||Apr 13, 2010||Warsaw Orthopedic, Inc.||System, devices and method for augmenting existing fusion constructs|
|US7771463||Nov 2, 2005||Aug 10, 2010||Ton Dai T||Twist-down implant delivery technologies|
|US7776075 *||Jan 31, 2006||Aug 17, 2010||Warsaw Orthopedic, Inc.||Expandable spinal rods and methods of use|
|US7785361||Mar 23, 2004||Aug 31, 2010||Julian Nikolchev||Implant delivery technologies|
|US7806900||Apr 26, 2007||Oct 5, 2010||Illuminoss Medical, Inc.||Apparatus and methods for delivery of reinforcing materials to bone|
|US7811284||Sep 20, 2007||Oct 12, 2010||Illuminoss Medical, Inc.||Systems and methods for internal bone fixation|
|US7862602||Dec 20, 2005||Jan 4, 2011||Biosensors International Group, Ltd||Indirect-release electrolytic implant delivery systems|
|US7879041||Oct 31, 2008||Feb 1, 2011||Illuminoss Medical, Inc.||Systems and methods for internal bone fixation|
|US7909873||Dec 14, 2007||Mar 22, 2011||Soteira, Inc.||Delivery apparatus and methods for vertebrostenting|
|US7918878||Aug 23, 2007||Apr 5, 2011||Pioneer Surgical Technology, Inc.||Minimally invasive surgical system|
|US7922727||Aug 23, 2007||Apr 12, 2011||Pioneer Surgical Technology, Inc.||Minimally invasive surgical system|
|US7922750||Nov 29, 2007||Apr 12, 2011||Paradigm Spine, Llc||Interlaminar-interspinous vertebral stabilization system|
|US7931676||Jan 18, 2007||Apr 26, 2011||Warsaw Orthopedic, Inc.||Vertebral stabilizer|
|US7931689||Mar 19, 2004||Apr 26, 2011||Spineology Inc.||Method and apparatus for treating a vertebral body|
|US7935134||Jun 29, 2006||May 3, 2011||Exactech, Inc.||Systems and methods for stabilization of bone structures|
|US7959634||Mar 28, 2005||Jun 14, 2011||Soteira Inc.||Orthopedic surgery access devices|
|US7998175||Jan 10, 2005||Aug 16, 2011||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US8002826||Oct 14, 2009||Aug 23, 2011||Medtronic Corevalve Llc||Assembly for placing a prosthetic valve in a duct in the body|
|US8012182||Mar 22, 2007||Sep 6, 2011||Zimmer Spine S.A.S.||Semi-rigid linking piece for stabilizing the spine|
|US8012201||May 5, 2005||Sep 6, 2011||Direct Flow Medical, Inc.||Translumenally implantable heart valve with multiple chamber formed in place support|
|US8012207||Mar 10, 2005||Sep 6, 2011||Vertiflex, Inc.||Systems and methods for posterior dynamic stabilization of the spine|
|US8016869||Dec 24, 2003||Sep 13, 2011||Biosensors International Group, Ltd.||Guidewire-less stent delivery methods|
|US8025680||May 17, 2006||Sep 27, 2011||Exactech, Inc.||Systems and methods for posterior dynamic stabilization of the spine|
|US8062368||Apr 24, 2008||Nov 22, 2011||Warsaw Orthopedic, Inc.||Expandable vertebral implants and methods of use|
|US8075595||Dec 6, 2004||Dec 13, 2011||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US8096996||Mar 19, 2008||Jan 17, 2012||Exactech, Inc.||Rod reducer|
|US8123807||Dec 6, 2004||Feb 28, 2012||Vertiflex, Inc.||Systems and methods for posterior dynamic stabilization of the spine|
|US8128662||Oct 18, 2006||Mar 6, 2012||Vertiflex, Inc.||Minimally invasive tooling for delivery of interspinous spacer|
|US8133213||Oct 18, 2007||Mar 13, 2012||Direct Flow Medical, Inc.||Catheter guidance through a calcified aortic valve|
|US8152837||Dec 20, 2005||Apr 10, 2012||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US8162985||Oct 20, 2004||Apr 24, 2012||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US8177817||Jul 8, 2005||May 15, 2012||Stryker Spine||System and method for orthopedic implant configuration|
|US8192439||Aug 23, 2007||Jun 5, 2012||Pioneer Surgical Technology, Inc.||Minimally invasive surgical system|
|US8210729||Apr 6, 2010||Jul 3, 2012||Illuminoss Medical, Inc.||Attachment system for light-conducting fibers|
|US8226690||Feb 23, 2006||Jul 24, 2012||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for stabilization of bone structures|
|US8246628 *||Sep 3, 2010||Aug 21, 2012||Illuminoss Medical, Inc.||Apparatus for delivery of reinforcing materials to bone|
|US8267969||Mar 20, 2007||Sep 18, 2012||Exactech, Inc.||Screw systems and methods for use in stabilization of bone structures|
|US8273116||Nov 30, 2010||Sep 25, 2012||Biosensors International Group, Ltd.||Indirect-release electrolytic implant delivery systems|
|US8308796||Jul 10, 2007||Nov 13, 2012||Direct Flow Medical, Inc.||Method of in situ formation of translumenally deployable heart valve support|
|US8317864||Feb 4, 2005||Nov 27, 2012||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US8328402||Jun 29, 2012||Dec 11, 2012||Illuminoss Medical, Inc.||Attachment system for light-conducting fibers|
|US8328848||Sep 26, 2006||Dec 11, 2012||Paradigm Spine, Llc||Interspinous vertebral stabilization devices|
|US8348956||Sep 20, 2010||Jan 8, 2013||Illuminoss Medical, Inc.||Apparatus and methods for reinforcing bone|
|US8357181||Oct 27, 2005||Jan 22, 2013||Warsaw Orthopedic, Inc.||Intervertebral prosthetic device for spinal stabilization and method of implanting same|
|US8366711||Aug 18, 2010||Feb 5, 2013||Illuminoss Medical, Inc.||Systems and methods for internal bone fixation|
|US8377118||May 5, 2005||Feb 19, 2013||Direct Flow Medical, Inc.||Unstented heart valve with formed in place support structure|
|US8394126 *||Sep 25, 2008||Mar 12, 2013||Biedermann Technologies Gmbh & Co. Kg||Bone anchoring device and bone stabilization device including the same|
|US8403968||Dec 26, 2007||Mar 26, 2013||Illuminoss Medical, Inc.||Apparatus and methods for repairing craniomaxillofacial bones using customized bone plates|
|US8409282||Jul 26, 2005||Apr 2, 2013||Vertiflex, Inc.||Systems and methods for posterior dynamic stabilization of the spine|
|US8425559||Nov 7, 2006||Apr 23, 2013||Vertiflex, Inc.||Systems and methods for posterior dynamic stabilization of the spine|
|US8470000||Apr 7, 2006||Jun 25, 2013||Paradigm Spine, Llc||Interspinous vertebral and lumbosacral stabilization devices and methods of use|
|US8512338||Apr 7, 2010||Aug 20, 2013||Illuminoss Medical, Inc.||Photodynamic bone stabilization systems and methods for reinforcing bone|
|US8523865||Jan 16, 2009||Sep 3, 2013||Exactech, Inc.||Tissue splitter|
|US8546456||Jul 24, 2009||Oct 1, 2013||Smith & Nephew, Inc.||Fracture fixation systems|
|US8551141||Aug 23, 2007||Oct 8, 2013||Pioneer Surgical Technology, Inc.||Minimally invasive surgical system|
|US8551142||Dec 13, 2010||Oct 8, 2013||Exactech, Inc.||Methods for stabilization of bone structures|
|US8556881||Feb 8, 2012||Oct 15, 2013||Direct Flow Medical, Inc.||Catheter guidance through a calcified aortic valve|
|US8568477 *||Jun 7, 2006||Oct 29, 2013||Direct Flow Medical, Inc.||Stentless aortic valve replacement with high radial strength|
|US8574233||Sep 14, 2012||Nov 5, 2013||Illuminoss Medical, Inc.||Photodynamic bone stabilization systems and methods for reinforcing bone|
|US8579954||Jan 27, 2006||Nov 12, 2013||Biosensors International Group, Ltd.||Untwisting restraint implant delivery system|
|US8623025||Jan 15, 2010||Jan 7, 2014||Gmedelaware 2 Llc||Delivery apparatus and methods for vertebrostenting|
|US8628570||Aug 18, 2011||Jan 14, 2014||Medtronic Corevalve Llc||Assembly for placing a prosthetic valve in a duct in the body|
|US8628574||Jul 27, 2010||Jan 14, 2014||Vertiflex, Inc.||Systems and methods for posterior dynamic stabilization of the spine|
|US8641719||Apr 8, 2011||Feb 4, 2014||Pioneer Surgical Technology, Inc.||Minimally invasive surgical system|
|US8657856||Aug 30, 2010||Feb 25, 2014||Pioneer Surgical Technology, Inc.||Size transition spinal rod|
|US8657870||Jun 26, 2009||Feb 25, 2014||Biosensors International Group, Ltd.||Implant delivery apparatus and methods with electrolytic release|
|US8668701 *||Jul 30, 2012||Mar 11, 2014||Illuminoss Medical, Inc.||Apparatus for delivery of reinforcing materials to bone|
|US8672982||Feb 21, 2013||Mar 18, 2014||Illuminoss Medical, Inc.||Apparatus and methods for repairing craniomaxillofacial bones using customized bone plates|
|US8684965||Apr 18, 2011||Apr 1, 2014||Illuminoss Medical, Inc.||Photodynamic bone stabilization and drug delivery systems|
|US8728125||Jul 15, 2010||May 20, 2014||Warsaw Orthopedic, Inc||Expandable spinal rods and methods of use|
|US8734460||Jan 3, 2011||May 27, 2014||Illuminoss Medical, Inc.||Systems and methods for internal bone fixation|
|US8740948||Dec 15, 2010||Jun 3, 2014||Vertiflex, Inc.||Spinal spacer for cervical and other vertebra, and associated systems and methods|
|US8771318||Feb 12, 2010||Jul 8, 2014||Stryker Spine||Rod inserter and rod with reduced diameter end|
|US8801800||Nov 19, 2010||Aug 12, 2014||Zimmer Knee Creations, Inc.||Bone-derived implantable devices and tool for subchondral treatment of joint pain|
|US8821504||Nov 19, 2010||Sep 2, 2014||Zimmer Knee Creations, Inc.||Method for treating joint pain and associated instruments|
|US8845726||Jan 22, 2009||Sep 30, 2014||Vertiflex, Inc.||Dilator|
|US8864768||Nov 19, 2010||Oct 21, 2014||Zimmer Knee Creations, Inc.||Coordinate mapping system for joint treatment|
|US8864828||Jan 15, 2009||Oct 21, 2014||Vertiflex, Inc.||Interspinous spacer|
|US8870965||Aug 19, 2010||Oct 28, 2014||Illuminoss Medical, Inc.||Devices and methods for bone alignment, stabilization and distraction|
|US8894655||Sep 25, 2006||Nov 25, 2014||Stryker Spine||Rod contouring apparatus and method for percutaneous pedicle screw extension|
|US8900271||May 1, 2012||Dec 2, 2014||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US8900285||Jan 27, 2006||Dec 2, 2014||Biosensors International Group, Ltd.||Covering electrolytic restraint implant delivery systems|
|US8906030||Sep 14, 2012||Dec 9, 2014||Illuminoss Medical, Inc.||Systems and methods for internal bone fixation|
|US8906031 *||Dec 28, 2012||Dec 9, 2014||Illuminoss Medical, Inc.||Systems and methods for internal bone fixation|
|US8906032||Nov 19, 2010||Dec 9, 2014||Zimmer Knee Creations, Inc.||Instruments for a variable angle approach to a joint|
|US8915966||Sep 14, 2012||Dec 23, 2014||Illuminoss Medical, Inc.||Devices and methods for bone alignment, stabilization and distraction|
|US8920473||Dec 7, 2007||Dec 30, 2014||Paradigm Spine, Llc||Posterior functionally dynamic stabilization system|
|US8936382||Sep 13, 2012||Jan 20, 2015||Illuminoss Medical, Inc.||Attachment system for light-conducting fibers|
|US8936644||Oct 19, 2012||Jan 20, 2015||Illuminoss Medical, Inc.||Systems and methods for joint stabilization|
|US8939977||Mar 13, 2013||Jan 27, 2015||Illuminoss Medical, Inc.||Systems and methods for separating bone fixation devices from introducer|
|US8961516||Sep 13, 2012||Feb 24, 2015||Sonoma Orthopedic Products, Inc.||Straight intramedullary fracture fixation devices and methods|
|US8974509||Jan 27, 2006||Mar 10, 2015||Biosensors International Group, Ltd.||Pass-through restraint electrolytic implant delivery systems|
|US8979851||Sep 25, 2013||Mar 17, 2015||Stryker Spine||Rod contouring apparatus for percutaneous pedicle screw extension|
|US9005254||Jan 24, 2014||Apr 14, 2015||Illuminoss Medical, Inc.||Methods for repairing craniomaxillofacial bones using customized bone plate|
|US9023084||Dec 6, 2004||May 5, 2015||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for stabilizing the motion or adjusting the position of the spine|
|US9033987||Dec 30, 2013||May 19, 2015||Zimmer Knee Creations, Inc.||Navigation and positioning instruments for joint repair|
|US9033988||Dec 30, 2013||May 19, 2015||Pioneer Surgical Technology, Inc.||Minimally invasive surgical system|
|US9039742||Apr 9, 2012||May 26, 2015||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US9060820||Sep 13, 2012||Jun 23, 2015||Sonoma Orthopedic Products, Inc.||Segmented intramedullary fracture fixation devices and methods|
|US9119680||Feb 27, 2012||Sep 1, 2015||Vertiflex, Inc.||Interspinous spacer|
|US9119684||Sep 25, 2013||Sep 1, 2015||Stryker Spine||Rod contouring method for percutaneous pedicle screw extension|
|US9119721||Aug 7, 2014||Sep 1, 2015||Zimmer Knee Creations, Inc.||Method for treating joint pain and associated instruments|
|US9125692||Feb 25, 2013||Sep 8, 2015||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US9125706||Nov 24, 2014||Sep 8, 2015||Illuminoss Medical, Inc.||Devices and methods for bone alignment, stabilization and distraction|
|US9144442||Jul 19, 2012||Sep 29, 2015||Illuminoss Medical, Inc.||Photodynamic articular joint implants and methods of use|
|US9149357||Dec 23, 2013||Oct 6, 2015||Medtronic CV Luxembourg S.a.r.l.||Heart valve assemblies|
|US9155570||Sep 14, 2012||Oct 13, 2015||Vertiflex, Inc.||Interspinous spacer|
|US9155572||Mar 6, 2012||Oct 13, 2015||Vertiflex, Inc.||Minimally invasive tooling for delivery of interspinous spacer|
|US9155574||Sep 28, 2009||Oct 13, 2015||Sonoma Orthopedic Products, Inc.||Bone fixation device, tools and methods|
|US9161783||Sep 14, 2012||Oct 20, 2015||Vertiflex, Inc.||Interspinous spacer|
|US9173746||Dec 10, 2012||Nov 3, 2015||Paradigm Spine, Llc||Interspinous vertebral stabilization devices|
|US9179959||Dec 22, 2011||Nov 10, 2015||Illuminoss Medical, Inc.||Systems and methods for treating conditions and diseases of the spine|
|US9186186||Apr 18, 2014||Nov 17, 2015||Vertiflex, Inc.||Spinal spacer for cervical and other vertebra, and associated systems and methods|
|US9192397||Jun 17, 2009||Nov 24, 2015||Gmedelaware 2 Llc||Devices and methods for fracture reduction|
|US9211146||Feb 27, 2012||Dec 15, 2015||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US9220540||Feb 15, 2013||Dec 29, 2015||Biedermann Technologies Gmbh & Co. Kg||Bone anchoring device and bone stabilization device including the same|
|US9220554 *||Feb 18, 2010||Dec 29, 2015||Globus Medical, Inc.||Methods and apparatus for treating vertebral fractures|
|US9237908||Apr 21, 2006||Jan 19, 2016||Spine Wave, Inc.||Dynamic stabilization system for the spine|
|US9237916||Dec 14, 2007||Jan 19, 2016||Gmedeleware 2 Llc||Devices and methods for vertebrostenting|
|US9247977||Dec 15, 2008||Feb 2, 2016||Stryker European Holdings I, Llc||Rod contouring apparatus for percutaneous pedicle screw extension|
|US9254156 *||Feb 3, 2014||Feb 9, 2016||Illuminoss Medical, Inc.||Apparatus for delivery of reinforcing materials to bone|
|US9254195||Nov 21, 2014||Feb 9, 2016||Illuminoss Medical, Inc.||Systems and methods for joint stabilization|
|US9259250||Apr 11, 2013||Feb 16, 2016||Sonoma Orthopedic Products, Inc.||Fracture fixation device, tools and methods|
|US9259257||Nov 19, 2010||Feb 16, 2016||Zimmer Knee Creations, Inc.||Instruments for targeting a joint defect|
|US9265549||Jan 27, 2014||Feb 23, 2016||Illuminoss Medical, Inc.||Apparatus for delivery of reinforcing materials to bone|
|US9271835||Dec 17, 2013||Mar 1, 2016||Zimmer Knee Creations, Inc.||Implantable devices for subchondral treatment of joint pain|
|US9283005||Feb 25, 2013||Mar 15, 2016||Vertiflex, Inc.||Systems and methods for posterior dynamic stabilization of the spine|
|US9308360||Dec 22, 2010||Apr 12, 2016||Direct Flow Medical, Inc.||Translumenally implantable heart valve with formed in place support|
|US9314279||Oct 23, 2012||Apr 19, 2016||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US9351746||Oct 7, 2014||May 31, 2016||Zimmer Knee Creations, Inc.||Coordinate mapping system for joint treatment|
|US9351835||May 28, 2015||May 31, 2016||Zimmer Knee Creations, Inc.||Method for treating joint pain and associated instruments|
|US9386996||Apr 24, 2015||Jul 12, 2016||Zimmer Knee Creations, Inc.||Navigation and positioning instruments for joint repair|
|US9393055||Nov 25, 2013||Jul 19, 2016||Vertiflex, Inc.||Spacer insertion instrument|
|US9402657||Jun 25, 2013||Aug 2, 2016||Paradigm Spine, Llc||Interspinous vertebral and lumbosacral stabilization devices and methods of use|
|US9427289||Oct 31, 2008||Aug 30, 2016||Illuminoss Medical, Inc.||Light source|
|US9433450||Nov 7, 2014||Sep 6, 2016||Illuminoss Medical, Inc.||Systems and methods for internal bone fixation|
|US9439765||Aug 6, 2014||Sep 13, 2016||Zimmer Knee Creations, Inc.||Method for subchondral treatment of joint pain using implantable devices|
|US9445843||Jan 13, 2014||Sep 20, 2016||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US9445897||Feb 26, 2013||Sep 20, 2016||Direct Flow Medical, Inc.||Prosthetic implant delivery device with introducer catheter|
|US9480485||Mar 23, 2010||Nov 1, 2016||Globus Medical, Inc.||Devices and methods for vertebrostenting|
|US9510875||Mar 12, 2014||Dec 6, 2016||Stryker European Holdings I, Llc||Systems and methods for percutaneous spinal fusion|
|US9510941||Mar 22, 2011||Dec 6, 2016||Direct Flow Medical, Inc.||Method of treating a patient using a retrievable transcatheter prosthetic heart valve|
|US9522018||Dec 29, 2014||Dec 20, 2016||Paradigm Spine, Llc||Posterior functionally dynamic stabilization system|
|US9532812||Sep 16, 2014||Jan 3, 2017||Vertiflex, Inc.||Interspinous spacer|
|US9566086||Sep 25, 2014||Feb 14, 2017||VeriFlex, Inc.||Dilator|
|US9572603||Sep 14, 2012||Feb 21, 2017||Vertiflex, Inc.||Interspinous spacer|
|US9572661||Mar 10, 2011||Feb 21, 2017||Direct Flow Medical, Inc.||Profile reduction of valve implant|
|US20040049189 *||Jul 25, 2001||Mar 11, 2004||Regis Le Couedic||Flexible linking piece for stabilising the spine|
|US20040193178 *||Dec 24, 2003||Sep 30, 2004||Cardiomind, Inc.||Multiple joint implant delivery systems for sequentially-controlled implant deployment|
|US20050216018 *||Mar 28, 2005||Sep 29, 2005||Sennett Andrew R||Orthopedic surgery access devices|
|US20060025855 *||May 5, 2005||Feb 2, 2006||Lashinski Randall T||Translumenally implantable heart valve with multiple chamber formed in place support|
|US20060030850 *||Jul 19, 2005||Feb 9, 2006||Keegan Thomas E||Methods and apparatuses for percutaneous implant delivery|
|US20060084982 *||Oct 20, 2004||Apr 20, 2006||The Board Of Trustees Of The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US20060084984 *||Dec 6, 2004||Apr 20, 2006||The Board Of Trustees For The Leland Stanford Junior University||Systems and methods for posterior dynamic stabilization of the spine|
|US20060084987 *||Jan 10, 2005||Apr 20, 2006||Kim Daniel H||Systems and methods for posterior dynamic stabilization of the spine|
|US20060155296 *||Jan 9, 2006||Jul 13, 2006||Celonova Biosciences, Inc.||Three-dimensional implantable bone support|
|US20060247625 *||Apr 29, 2005||Nov 2, 2006||Sdgi Holdings, Inc.||System, devices and method for augmenting existing fusion constructs|
|US20060264934 *||Jul 8, 2005||Nov 23, 2006||Medicinelodge, Inc.||System and method for orthopedic implant configuration|
|US20060293663 *||Apr 21, 2006||Dec 28, 2006||Spine Wave, Inc.||Dynamic stabilization system for the spine|
|US20070043419 *||Mar 23, 2004||Feb 22, 2007||Cardiomind, Inc.||Implant delivery technologies|
|US20070161993 *||Sep 26, 2006||Jul 12, 2007||Lowery Gary L||Interspinous vertebral stabilization devices|
|US20070167949 *||Mar 20, 2007||Jul 19, 2007||Moti Altarac||Screw systems and methods for use in stabilization of bone structures|
|US20070173822 *||Jan 13, 2006||Jul 26, 2007||Sdgi Holdings, Inc.||Use of a posterior dynamic stabilization system with an intradiscal device|
|US20070191845 *||Jan 31, 2006||Aug 16, 2007||Sdgi Holdings, Inc.||Expandable spinal rods and methods of use|
|US20070191846 *||Jan 31, 2006||Aug 16, 2007||Aurelien Bruneau||Expandable spinal rods and methods of use|
|US20070233079 *||Sep 25, 2006||Oct 4, 2007||Stryker Spine||Rod contouring apparatus and method for percutaneous pedicle screw extension|
|US20070239159 *||Oct 25, 2006||Oct 11, 2007||Vertiflex, Inc.||Systems and methods for stabilization of bone structures|
|US20080015687 *||Jul 10, 2007||Jan 17, 2008||Direct Flow Medical, Inc.||Method of in situ formation of translumenally deployable heart valve support|
|US20080039839 *||Aug 23, 2007||Feb 14, 2008||Pioneer Laboratories, Inc.||Minimally invasive surgical system|
|US20080039840 *||Aug 23, 2007||Feb 14, 2008||Pioneer Laboratories, Inc.||Minimally invasive surgical system|
|US20080039943 *||May 24, 2005||Feb 14, 2008||Regis Le Couedic||Set For Treating The Degeneracy Of An Intervertebral Disc|
|US20080077136 *||Jan 9, 2007||Mar 27, 2008||Stryker Spine||Rod inserter and rod with reduced diameter end|
|US20080097441 *||May 17, 2006||Apr 24, 2008||Stanley Kyle Hayes||Systems and methods for posterior dynamic stabilization of the spine|
|US20080125784 *||Sep 20, 2007||May 29, 2008||Illuminoss Medical, Inc.||Systems and methods for internal bone fixation|
|US20080177318 *||Jan 18, 2007||Jul 24, 2008||Warsaw Orthopedic, Inc.||Vertebral Stabilizer|
|US20080200898 *||Oct 18, 2007||Aug 21, 2008||Lashinski Randall T||Catheter guidance through a calcified aortic valve|
|US20080228225 *||Nov 29, 2007||Sep 18, 2008||Paradigm Spine, Llc||Interlaminar-Interspinous Vertebral Stabilization System|
|US20080255560 *||May 20, 2005||Oct 16, 2008||Myers Surgical Solutions, Llc||Fracture Fixation and Site Stabilization System|
|US20080312694 *||Jun 15, 2007||Dec 18, 2008||Peterman Marc M||Dynamic stabilization rod for spinal implants and methods for manufacturing the same|
|US20090054900 *||Oct 31, 2008||Feb 26, 2009||Illuminoss Medical, Inc.||Systems and Methods for Internal Bone Fixation|
|US20090082857 *||May 5, 2005||Mar 26, 2009||Direct Flow Medical, Inc.||Unstented heart valve with formed in place support structure|
|US20090088836 *||Aug 22, 2008||Apr 2, 2009||Direct Flow Medical, Inc.||Translumenally implantable heart valve with formed in place support|
|US20090099605 *||Dec 15, 2008||Apr 16, 2009||Stryker Spine||Rod contouring apparatus for percutaneous pedicle screw extension|
|US20090125066 *||Dec 22, 2008||May 14, 2009||Gary Kraus||Facet stabilization schemes|
|US20090131983 *||Sep 25, 2008||May 21, 2009||Lutz Biedermann||Bone anchoring device and bone stabilization device including the same|
|US20090270987 *||Apr 24, 2008||Oct 29, 2009||Warsaw Orthopedic, Inc.||Expandable vertebral implants and methods of use|
|US20100010623 *||Jul 13, 2009||Jan 14, 2010||Direct Flow Medical, Inc.||Percutaneous heart valve with stentless support|
|US20100114169 *||Oct 27, 2009||May 6, 2010||Regis Le Couedic||Flexible linking piece for stabilising the spine|
|US20100114173 *||Oct 27, 2009||May 6, 2010||Le Couedic Regis||Flexible linking piece for stabilising the spine|
|US20100160968 *||Dec 19, 2008||Jun 24, 2010||Abbott Spine Inc.||Systems and methods for pedicle screw-based spine stabilization using flexible bands|
|US20100198265 *||Apr 8, 2010||Aug 5, 2010||Morrison Matthew M||System, Devices and method for augmenting existing fusion constructs|
|US20100256641 *||Dec 26, 2007||Oct 7, 2010||Illuminoss Medical, Inc.||Apparatus and Methods for Repairing Craniomaxillofacial Bones Using Customized Bone Plates|
|US20100262069 *||Apr 7, 2010||Oct 14, 2010||Illuminoss Medical, Inc.||Photodynamic Bone Stabilization Systems and Methods for Reinforcing Bone|
|US20100265733 *||Apr 6, 2010||Oct 21, 2010||Illuminoss Medical, Inc.||Attachment System for Light-Conducting Fibers|
|US20100280553 *||Jul 15, 2010||Nov 4, 2010||Warsaw Orthopedic, Inc.||Expandable Spinal Rods and Methods of Use|
|US20100312279 *||Aug 23, 2007||Dec 9, 2010||Gephart Matthew P||Minimally Invasive Surgical System|
|US20100331850 *||Sep 3, 2010||Dec 30, 2010||Illuminoss Medical, Inc.||Apparatus for delivery of reinforcing materials to bone|
|US20110004213 *||Aug 18, 2010||Jan 6, 2011||IlluminOss Medical , Inc.||Systems and methods for internal bone fixation|
|US20110009871 *||Sep 20, 2010||Jan 13, 2011||Illuminoss Medical, Inc.||Apparatus and methods for reinforcing bone|
|US20110054535 *||Aug 30, 2010||Mar 3, 2011||Gephart Matthew P||Size Transition Spinal Rod|
|US20110125272 *||Nov 19, 2010||May 26, 2011||Knee Creations, Llc||Bone-derived implantable devices for subchondral treatment of joint pain|
|US20110190776 *||Dec 20, 2010||Aug 4, 2011||Palmaz Scientific, Inc.||Interosteal and intramedullary implants and method of implanting same|
|US20110202062 *||Feb 18, 2010||Aug 18, 2011||O'halloran Damien||Methods and Apparatus For Treating Vertebral Fractures|
|US20120289968 *||Jul 30, 2012||Nov 15, 2012||Illuminoss Medical, Inc.||Apparatus for Delivery of Reinforcing Materials to Bone|
|US20130184715 *||Dec 28, 2012||Jul 18, 2013||Illuminoss Medical, Inc.||Systems and Methods for Internal Bone Fixation|
|US20140148813 *||Feb 3, 2014||May 29, 2014||Illuminoss Medical, Inc.||Apparatus for Delivery of Reinforcing Materials to Bone|
|US20140277169 *||Mar 14, 2013||Sep 18, 2014||Nadi Salah Hibri||Vertebral Implant|
|EP2740423A1||Apr 26, 2007||Jun 11, 2014||Illuminoss Medical, Inc.||Apparatus for delivery of reinforcing materials to a fractured long bone|
|WO2006116119A2 *||Apr 21, 2006||Nov 2, 2006||Spine Wave, Inc.||Dynamic stabilization system for the spine|
|WO2006116119A3 *||Apr 21, 2006||Nov 15, 2007||Spine Wave Inc||Dynamic stabilization system for the spine|
|U.S. Classification||606/86.00A, 606/262|
|International Classification||A61B17/17, A61B17/00, A61B17/86, A61B17/70, A61B17/16, A61B17/60, A61B17/88, A61F2/46, A61B17/56, A61B17/58, A61F2/44, A61L27/00, A61B, A61L27/34|
|Cooperative Classification||A61B17/1757, A61B17/7008, A61B17/8863, A61B17/1671, A61B17/7013, A61B17/7002, A61B17/1796, A61B2017/00557, A61B17/7049, A61F2/4611, A61B17/7001, A61B17/60, A61B17/7083, A61B17/864, A61B17/1697|
|European Classification||A61B17/16S4, A61F2/46B7, A61B17/70B1, A61B17/16W, A61B17/60, A61B17/88F, A61B17/70T4|
|Jun 25, 2003||AS||Assignment|
Owner name: VERTELINK CORPORATION, CALIFORNIA
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|Apr 8, 2005||AS||Assignment|
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